Electric and acoustic stimulation fitting systems and methods

ABSTRACT

Methods and systems for modifying the parameters of at least one hearing device for a patient with residual hearing provide needed orchestration of acoustic and electric stimulation of patients wearing such devices.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a divisional of U.S. patent application Ser. No.11/097,611 now U.S. Pat. No. 7,561,920, filed on Mar. 31, 2005, whichclaims the benefit of U.S. Provisional Application No. 60/559,297, filedon Apr. 2, 2004, which applications are incorporated herein byreference.

FIELD OF THE INVENTION

The present invention relates to cochlear implant systems and methods,and more particularly relates to methods and systems for modifying theparameters of at least one hearing device for a patient with residualhearing.

BACKGROUND OF THE INVENTION

The present invention is related to U.S. patent application Ser. No.10/218,645, filed Aug. 13, 2002, U.S. patent application Ser. No.10/647,372, filed Aug. 25, 2003, and U.S. patent application Ser. No10/651,653, filed Aug. 29, 2003; all of which share the sole commonassignee, Advanced Bionics Corporation of Valencia, Calif., and arehereby incorporated by reference in their respective entireties into thedescription of the present invention.

Cochlear prostheses, or cochlear implants, produce sensations of soundin deaf or partially-deaf patients by direct electrical stimulation ofthe auditory nerve. Cochlear implants have been used in conjunction withhearing aids for partially deaf patients. In modern, multichannelcochlear implants, several different sites are stimulated at variousdistances along the cochlea to evoke the different pitches of soundperception that are normally encoded by nerve activity originating fromthe respective sites. The patterns of electrical stimulation are derivedfrom acoustic signals picked up by a microphone and transformed by aso-called speech processor that is programmed to meet the particularrequirements of each patient. Several different schemes, or fittingtechniques and/or systems as described below, for processing theacoustic signal and transforming it into electrical stimuli have beendeveloped and are well-described in the scientific literature andvarious patents.

Electrical stimulation of predetermined locations within the cochlea ofthe human ear through an intra-cochlear electrode array is described,e.g., in U.S. Pat. No. 4,400,590. The electrode array shown in the '590patent comprises a plurality of exposed electrode pairs spaced along andimbedded in a resilient curved base for implantation in accordance witha method of surgical implantation, e.g., as described in U.S. Pat. No.3,751,605. The system described in the '590 patent receives audiosignals, i.e., sound waves, at a signal processor (or speech processor)located outside the body of a hearing impaired patient. The speechprocessor converts the received audio signals into modulated RF datasignals that are transmitted through the patient's skin and then by acable connection to an implanted multi-channel intra-cochlear electrodearray. The modulated RF signals are demodulated into analog signals andare applied to selected ones of the plurality of exposed electrode pairsin the intra-cochlear electrode so as to electrically stimulatepredetermined locations of the auditory nerve within the cochlea.

U.S. Pat. No. 5,938,691, incorporated herein by reference, shows animproved multi-channel cochlear stimulation system employing animplanted cochlear stimulator (ICS) and an externally wearable speechprocessor (SP). The speech processor employs a headpiece that is placedadjacent to the ear of the patient, which receives audio signals andtransmits the audio signals back to the speech processor. The speechprocessor receives and processes the audio signals and generates dataindicative of the audio signals for transcutaneous transmission to theimplantable cochlear stimulator. The implantable cochlear stimulatorreceives the transmission from the speech processor and appliesstimulation signals to a plurality of cochlear stimulating channels,each having a pair of electrodes in an electrode array associatedtherewith. Each of the cochlear stimulating channels uses a capacitor tocouple the electrodes of the electrode array.

A new, more sophisticated, class of cochlear implant, referred to as abionic ear, is now available, providing patients with enhanced hearingperformance. For example, Advanced Bionics Corporation, of Valencia,California, currently offers a cochlear implant which it refers to asthe CII Bionic Ear® cochlear implant. Many features associated with theCII Bionic Ear implant are described in U.S. Pat. No. 6,219,580,incorporated herein by reference. The added complexity of the CII BionicEar cochlear implant includes higher numbers of channels, arbitrarysimultaneous grouping, intra-phase gaps, binaural capabilities, and thelike. The Bionic Ear implant contains advances in, e.g., internal memorybanks, that enable it to send very detailed, high resolution soundsignals to the auditory nerve. Such signals are delivered to theauditory nerve using a special electrode adapted to be inserted into thecochlea. A representative electrode usable with the CII Bionic Ear isdescribed in U.S. Pat. No. 6,129,753, also incorporated herein byreference.

Other improved features of cochlear implant systems are taught, e.g., inU.S. Pat. Nos. 5,626,629; 6,067,474; 6,157,861; 6,249,704; and6,289,247, each of which is incorporated herein by reference.

The implantable cochlear stimulators described in at least the '629,'474, '861, '580, and '704 patents are able to selectively control thepulse amplitude and pulse width of stimulating pulses that are appliedthrough the electrode array to the cochlea, and the frequency at whichthe stimulating pulses are applied.

When a cochlear prosthesis is first provided to a patient, it isnecessary to initially “fit” or “adjust” the prosthesis. As used herein,it should be noted that the terms “fit”, “adjust”, “fitting”,“adjusting”, “program”, or “programming” relate to making electronic orsoftware programming changes to the prosthesis, as opposed to makingphysical or hardware changes. Proper fitting allows the prosthesis tobetter perform its intended function of helping the patient to sensesound.

As the art of cochlear stimulation has advanced, the implanted portionof the cochlear stimulation system, and the externally wearableprocessor (or speech processor), have become increasingly complicatedand sophisticated. In addition, much of the circuitry previouslyemployed in the externally wearable processor has been moved to theimplanted portion, thereby reducing the amount of information that mustbe transmitted from the external wearable processor to the implantedportion. The amount of control and discretion exercisable by anaudiologist in selecting the modes and methods of operation of thecochlear stimulation system have increased dramatically and it is nolonger possible to fully control and customize the operation of thecochlear stimulation system through the use of, for example, switcheslocated on the speech processor. As a result, it has become necessary toutilize an implantable cochlear stimulator fitting system to establishthe operating modes and methods of the cochlear stimulation system andthen to download such programming into the speech processor. One suchfitting system is described in the '629 patent. An improved fittingsystem is described in the '247 patent.

The '247 patent describes representative stimulation strategies (a.k.a.,speech processing strategies) that may be employed by a multichannelstimulation system. Such strategies define patterns of stimulationwaveforms that are to be applied to the electrodes as controlledelectrical currents. For instance, the speech processing strategy isused, inter alia, to condition the magnitude and polarity of thestimulation current applied to the implanted electrodes of the electrodearray. If multiple electrode pairs exist, as is the case with amultichannel cochlear stimulator, then the types of stimulation patternsapplied to the multiple channels may be broadly classified as: (1)simultaneous stimulation patterns (substantially all electrodes receivecurrent stimuli at the same time, thereby approximating an analogsignal), or (2) sequential or non-simultaneous stimulation patterns(only one electrode receives a current pulse at one time). Simultaneousstimulation patterns may be “fully” simultaneous or partiallysimultaneous. A fully simultaneous stimulation pattern is one whereinstimulation currents, either analog or pulsatile, are applied to theelectrodes of all of the available channels at the same time. Apartially simultaneous stimulation pattern is one where stimulationcurrents, either analog or pulsatile, are applied to the electrodes oftwo or more channels, but not necessarily all of the channels, at thesame time.

Acoustic transducers, such as earphone hearing instruments or hearingaids, can be used by patients with residual hearing in conjunction withcochlear prosthesis in either the same ear (ipsilater ear) as thecochlear implant or the opposite ear (contralateral ear). Examples ofsuch acoustic transducers include U.S. Pat. Nos. 6,700,983; 6,658,125;6,522,764; 5,201,006; 5,033,090; 5,357,576; 5,204,917; and 4,051,330;which patents are incorporated herein in their entireties by reference.

As mentioned above, auditory clinicians currently apply various systemsand methods for modifying the various parameters of, or for fitting,cochlear prostheses. Similarly, auditory clinicians apply varioussystems and methods for modifying the various parameters of hearingaids. However, there are currently no established systems and methodswhich simultaneously or sequentially modify the parameters of bothcochlear prostheses and hearing aids in a patient using both systems.

A need exists for a technique and system for programming, or fitting, ahearing device configured to deliver electric stimulation to a patientand a hearing device configured to deliver acoustic stimulation to thepatient.

BRIEF SUMMARY OF THE INVENTION

The present invention is directed to fitting systems and techniques thatmay be used to fit a variety of cochlear implants and a variety ofhearing aids, such as those mentioned above, during the same fittingsession. The present invention addresses the above and other needs byproviding a method for modifying the parameters of multiple hearingdevices for a patient with residual hearing, a system for modifying theparameters of acoustic and electric stimulation hearing devices, and amethod for modifying the parameters of at least one hearing device.

In an example embodiment, a method for modifying the parameters of atleast one hearing device includes receiving electric and acousticstimulation data from at least one hearing device to a computer withsoftware, assessing electric and acoustic stimulation parameters andpatterns based on the stimulation data, and delivering the electric andacoustic stimulation parameters and patterns to the at least one hearingdevice.

In another embodiment, the method further includes mapping thestimulation data with the software.

In another embodiment, assessing electric and acoustic stimulationparameters and patterns based on the stimulation data includes assessingthe proper sequencing of acoustic and electric events for at least oneof a hearing aid and the acoustic elements of an electric-acousticprocessor and at least one of a cochlear implant speech processor andthe electric elements of an electric-acoustic processor.

In another embodiment, delivering the electric and acoustic stimulationparameters and patterns to the at least one hearing device includes atleast one of simultaneously and sequentially outputting instructionscapable of modifying acoustic and electric parameters to determineinteraction between multiple channels in at least one of a hearing aid,the acoustic elements of an electric-acoustic processor, a cochlearimplant speech processor, and the electric elements of anelectric-acoustic processor.

In another embodiment, the at least one hearing device comprises twohearing devices configured to be worn contralateral to each other by apatient.

In an example embodiment, a method for modifying the parameters ofmultiple hearing devices includes providing a user interface that allowsa user to modify parameters of at least one of a hearing aid and theacoustic elements of an electric-acoustic processor and at least one ofa cochlear implant speech processor and the electric elements of anelectric-acoustic processor using software configured to provideinstructions for at least one of acoustic stimulation to the hearingaid, electric stimulation to the cochlear implant speech processor,electric stimulation to the electric-acoustic processor, and acousticstimulation to the electric-acoustic processor.

In another embodiment, the user interface is configured to allow theuser to modify, with the software, the parameters of theelectric-acoustic processor when the electric elements of theelectric-acoustic processor are situated ipsilateral to the acousticelements of the electric-acoustic processor.

In another embodiment, the software is configured to provideinstructions when the at least one of the hearing aid and the acousticelements of the electric-acoustic processor are situated contralateralto the at least one of the cochlear implant speech processor and theelectric elements of the electric-acoustic processor.

In another embodiment, the method further includes mapping audioinformation to electrode contact position with the software in a patientwith a cochlear implant.

In another embodiment, the method further includes at least one ofsimultaneously and sequentially outputting instructions capable ofmodifying acoustic and electric parameters to determine interactionbetween multiple channels in the at least one of the hearing aid, theacoustic elements of the electric-acoustic processor, the cochlearimplant speech processor, and the electric elements of theelectric-acoustic processor.

In another embodiment, the method further includes assessing, with thesoftware, the proper sequencing of acoustic and electric events for atleast one of the hearing aid and the acoustic elements of theelectric-acoustic processor and at least one of the cochlear implantspeech processor and the electric elements of the electric-acousticprocessor.

In an example embodiment, a system for modifying the parameters ofacoustic and electric stimulation hearing devices includes a computerprovided with access to software that is configured to communicate withand modify parameters of at least one of a hearing aid and the acousticelements of an electric-acoustic processor and at least one of acochlear implant speech processor and the electric elements of anelectric-acoustic processor.

In another embodiment, the system further includes a programminginterface unit configured to exchange information between the computerand at least one of the hearing aid, the cochlear implant speechprocessor, the electric elements of the electric-acoustic processor, andthe acoustic elements of the electric-acoustic processor.

In other embodiments, the computer is configured to communicate directlywith at least one of the hearing aid, the cochlear implant speechprocessor, the electric elements of the electric-acoustic processor, andthe acoustic elements of the electric-acoustic processor throughwireless and/or wired communications.

In another embodiment, the computer is configured to display data usedto at least one of map, evaluate, and modify the parameters of at leastone of the hearing aid, the acoustic elements of the electric-acousticprocessor, the cochlear implant speech processor, and the electricelements of the electric-acoustic processor.

In another embodiment, the software is scripted to evaluate datarelevant to operational parameters of at least one of the hearing aid,the acoustic elements of the electric-acoustic processor, the cochlearimplant speech processor, and the electric elements of theelectric-acoustic processor.

In another embodiment, the software is configured to map parameterlevels and ranges and is configured to map responses of a patientwearing the at least one of the hearing aid, the acoustic elements ofthe electric-acoustic processor, the cochlear implant speech processor,and the electric elements of the electric-acoustic processor.

In another embodiment, the computer is configured to simultaneously andsequentially output instructions capable of modifying acoustic andelectric stimulation parameters to determine interaction betweenmultiple channels in the at least one of the hearing aid, the acousticelements of the electric-acoustic processor, the cochlear implant speechprocessor, and the electric elements of the electric-acoustic processor.

In another embodiment, the software is scripted to provide a suggestedassessment of the proper sequencing of acoustic and electric events forat least one of the hearing aid and the acoustic elements of theelectric-acoustic processor and at least one of the cochlear implantspeech processor and the electric elements of the electric-acousticprocessor.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and other aspects of the present invention will be moreapparent from the following more particular description thereof,presented in conjunction with the following drawings and appendiceswherein:

FIG. 1 is a current stimulation waveform that defines the stimulationrate (1/T) and biphasic pulse width (PW) associated with electricalstimuli, as those terms are used in the present application;

FIGS. 2A and 2B respectively show a cochlear implant system and apartial functional block diagram of the cochlear stimulation system,which system is capable of providing high rate pulsitile electricalstimuli;

FIGS. 3A and 3B respectively show a conventional in-the-ear hearing aidand a behind-the-ear hearing aid;

FIGS. 4A-4C show different example embodiments of fitting systems;

FIG. 5 shows a software module for generating stimuli used during thesound processor setting procedure (or fitting process);

FIG. 6 is a flowchart of an example method for modifying the parametersof multiple hearing devices for a patient with residual hearing;

FIG. 7 is a flowchart of an example paradigm for the method of FIG. 6;and

FIG. 8 is a flowchart of another example paradigm for the method of FIG.6.

Corresponding reference characters indicate corresponding componentsthroughout the several views of the drawings.

DETAILED DESCRIPTION OF THE INVENTION

The following description is of the best mode presently contemplated forcarrying out the invention. This description is not to be taken in alimiting sense, but is made merely for the purpose of describing thegeneral principles of the invention. The scope of the invention shouldbe determined with reference to the claims.

FIG. 1 shows a waveform diagram of a biphasic pulse train, and definesstimulation rate, pulse width and pulse amplitude.

FIG. 2A shows a cochlear stimulation system, or cochlear prosthesis,that includes a speech processor portion 10 and a cochlear stimulationportion 12. The speech processor portion 10 includes a speech processor(SP) 16 and a microphone 18. The microphone 18 may be connected directlyto the SP 16, or may be coupled to the SP 16 through an appropriatecommunication link 24. An auxiliary input port 17 may also be part ofthe speech processor 16 to allow input signals from a source other thanthe microphone 18 to be input into the SP 16.

The cochlear stimulation portion 12 includes an implantable cochlearstimulator (ICS) 21 and an electrode array 48. The electrode array 48 isadapted to be inserted within the cochlea of a patient. The array 48includes a multiplicity of electrodes, e.g., sixteen electrodes, spacedalong its length that are selectively connected to the ICS 21. Theelectrode array 48 may be substantially as shown and described in U.S.Pat. Nos. 4,819,647 or 6,129,753, incorporated herein by reference.Electronic circuitry within the ICS 21 allows a specified stimulationcurrent to be applied to selected pairs or groups of the individualelectrodes included within the electrode array 48 in accordance with aspecified stimulation pattern, defined by the SP 16.

The ICS 21 and the SP 16 are shown in FIG. 2A as being linked togetherelectronically through a suitable data or communications link 14. Insome cochlear implant systems, the SP 16, auxiliary input port 17 andmicrophone 18 comprise the external portion of the cochlear implantsystem; and the ICS 21 and electrode array 48 comprise the implantableportion of the system. In an example embodiment, the data link 14 is atranscutaneous data link that allows power and control signals to besent from the SP 16 to the ICS 21. In some embodiments, data and statussignals may also be sent from the ICS 21 to the SP 16.

In some cochlear implant systems, as shown more particularly below inFIG. 2B, at least certain portions of the SP 16 are included within theimplantable portion of the overall cochlear implant system, while otherportions of the SP 16 remain in the external portion of the system. Invarious embodiments, at least the microphone 18 (and auxiliary inputport 17, if used) and associated analog front end (AFE) circuitry 22 arepart of the external portion of the system, and at least the ICS 21 andelectrode array 48 are part of the implantable portion of the invention.As used herein, “external” means not implanted under the skin orresiding within the inner ear. However, “external” may mean within theouter ear, including in the ear canal, and may also include within themiddle ear.

Typically, where a transcutaneous data link is to be established betweenthe external portion and implantable portions of the system, such a linkis realized by an internal antenna coil within the implantable portionand an external antenna coil within the external portion. In use, theexternal antenna coil is positioned so as to be aligned over thelocation where the internal antenna coil is implanted allowing the coilsto be inductively coupled to each other, thereby allowing data (e.g.,the magnitude and polarity of sensed acoustic signals) and power to betransmitted from the external portion to the implantable portion. Note,in other embodiments, both the SP 16 and the ICS 21 are implanted withinthe patient, either in the same housing or in separate housings. If inthe same housing, the link 14 can be realized with a direct wireconnection within such housing. If in separate housings, as taught,e.g., in U.S. Pat. No. 6,067,474, incorporated herein by reference, thelink 14 can be, for example, an inductive link using a coil or a wireloop coupled to the respective parts.

The microphone 18 senses acoustic signals and converts such sensedsignals to corresponding electrical signals, and thus can be consideredan acoustic transducer. The electrical signals are sent to the SP 16over a suitable electrical or other link 24. Alternatively, electricalsignals can be input directly into the auxiliary input port 17 from asuitable signal source. The SP 16 processes the converted acousticsignals received From the microphone, or the electrical signals receivedthrough the auxiliary input port 17, in accordance with a speechprocessing strategy (e.g., a selected speech processing strategy) inorder to generate appropriate control signals for controlling the ICS21. In operation, by way of example, such control signals specify ordefine the polarity, magnitude, location (which electrode pair receivesthe stimulation current), and timing (when the stimulation current isapplied to the electrode pair) of the stimulation current that isgenerated by the ICS. Such control signals thus combine to produce adesired spatiotemporal pattern of electrical stimuli in accordance withthe desired speech processing strategy. Unlike early cochlear implantsystems, cochlear implant systems according to various embodiments ofthe present invention advantageously confine such control signals tocircuitry within the implantable portion of the system, thereby avoidingthe need to continually send or transmit such control signals across atranscutaneous link.

The speech processing strategy is used, inter alia, to condition themagnitude and polarity of the stimulation current applied to theimplanted electrodes of the electrode array 48. A typical speechprocessing strategy involves defining a pattern of stimulation waveformsthat are to be applied to the electrodes as controlled electricalcurrents. In accordance with an example embodiment of the presentinvention, an auto-conditioning with high resolution (ACHR) strategy isused which stimulates the implanted electrodes with a high ratepulsitile pattern that is amplitude modulated by the sound information.If multiple electrode pairs exist, as is the case with a multichannelcochlear implant system, then the types of stimulation patterns appliedto the multiple channels may be conveniently categorized as: (1)simultaneous stimulation patterns, or (2) non-simultaneous stimulationpatterns. Simultaneous stimulation patterns may be “fully” simultaneousor partially simultaneous. A fully simultaneous stimulation pattern isone wherein stimulation currents, either analog or pulsitile, areapplied to the electrodes of all of the available channels at the sametime. A partially simultaneous stimulation pattern is one whereinstimulation currents, either analog or pulsitile, are applied to theelectrodes of two or more channels, but not necessarily all of thechannels, at the same time. Examples of each type are given in U.S. Pat.No. 6,289,247, incorporated herein by reference.

Analog waveforms used in analog stimulation patterns are typicallyreconstructed by the generation of continuous short monophasic pulses(samples). The sampling rate is selected to be fast enough to allow forproper reconstruction of the temporal details of the signal. An exampleof such a sampled analog stimulation pattern is a simultaneous analogsampler (SAS) strategy.

Current pulses applied in pulsitile stimulation patterns are generallybiphasic pulses, as shown in FIG. 1, but can also be multiphasic pulses,applied to the electrodes of each channel. The biphasic/multiphasicpulse has a magnitude (e.g., amplitude and/or duration) that varies as afunction of the sensed acoustic signal. (A “biphasic” pulse is generallyconsidered as two pulses: a first pulse of one polarity having aspecified magnitude, followed immediately, or after a very short delay,by a second pulse of the opposite polarity having the same total charge,which charge is the product of stimulus current times duration of eachpulse or phase.) For multichannel cochlear stimulators, a high ratebiphasic stimulation pulse train can be applied to each of the pairs ofelectrodes of selected channels in accordance with a selected strategy,and the pulse amplitude of the pulse train can be modulated as afunction of information contained within the sensed acoustic signal orthe received auxiliary input signal.

Turning next to FIG. 2B, a partial block diagram of a representativecochlear implant is shown. More particularly, FIG. 2B shows a partialfunctional block diagram of the SP 16 and the ICS 21 of an exemplecochlear implant system capable of providing a high rate pulsitilestimulation pattern. FIG. 2B depicts the functions that are carried outby the SP 16 and the ICS 21. The actual electronic circuitry used tocarry out these functions is not critical to understanding andpracticing the present invention. It should also be pointed out that theparticular functions shown in FIG. 2B are representative of just onetype of signal processing strategy that may be used (for dividing theincoming signal into frequency bands and independently processing eachband). Other signal processing strategies can also be used to processthe incoming acoustical signal.

A description of the functional block diagram of the cochlear implantsystem shown in FIG. 2B is provided in U.S. Pat. No. 6,219,580,incorporated herein by reference. It is to be appreciated that thefunctionality shown in FIG. 2B is only representative of one type ofexemple cochlear implant system and is not intended to be limiting. Thedetails associated with a given cochlear implant system are not criticalto understanding and practicing the present invention.

In the manner described in the U.S. Pat. No. 6,219,580 patent, thecochlear implant functionally shown in FIG. 2B provides n analysischannels that may be mapped to one or more stimulus channels. That is,as seen in FIG. 2B, after the incoming sound signal is received throughthe microphone 18 or auxiliary input port 17, and the analog front endcircuitry (AFE) 22, it is digitized in an analog to digital (A/D)converter 28, and then subjected to appropriate gain control (which mayinclude compression) in an automatic gain control (AGC) unit 29. (Itshould be noted that in some instances the signal input into theauxiliary input port 17 may already be digitized, in which case a signalpath 19 is provided that bypasses the A/D converter 28.) Afterappropriate gain control, the signal is divided into n analysischannels, each of which includes a bandpass filter, BPFn, centered at aselected frequency. The signal present in each analysis channel isprocessed as described more fully in the U.S. Pat. No. 6,219,580 patent,and the signals from each analysis channel are then mapped, usingmapping function 41, so that an appropriate stimulus current, of adesired amplitude and timing, can be applied through a selected stimuluschannel to stimulate the auditory nerve.

Thus it is seen that the system of FIG. 2B provides a multiplicity ofchannels, n, wherein the incoming signal is analyzed. The informationcontained in these n “analysis channels” is then appropriatelyprocessed, compressed and mapped in order to control the actual stimuluspatterns that are applied to the patient by the ICS 21 and itsassociated electrode array 48. The electrode array 48 includes amultiplicity of electrode contacts, connected through appropriateconductors, to respective current generators, or pulse generators,within the ICS. Through this multiplicity of electrode contacts, amultiplicity of stimulus channels, e.g., m stimulus channels, existthrough which individual electrical stimuli can be applied at mdifferent stimulation sites within the patient's cochlea.

In various example embodiments, a one-to-one mapping scheme between theanalysis channels and the stimulus channels is used, wherein n=m, andthe signal analyzed in the first analysis channel is mapped to produce astimulation current at the first stimulation channel, and so on. Inother example embodiments, a different mapping scheme may provebeneficial to the patient. For example, assume that n is not equal to m(n, for example, could be at least 20 or as high as 32, while m may beno greater than sixteen, e.g., 8 to 16). The signal resulting fromanalysis in the first analysis channel can be mapped, using appropriatemapping circuitry 41 or the like, to the first stimulation channel via afirst map link, resulting in a first stimulation site (or first area ofneural excitation). Similarly, the signal resulting from analysis in thesecond analysis channel of the SP can be mapped to the secondstimulation channel via a second map link, resulting in a secondstimulation site. Also, the signal resulting from analysis in the secondanalysis channel can be jointly mapped to the first and secondstimulation channels via a joint map link, which results in astimulation site that is somewhere in between the first and secondstimulation sites. The “in between site” can be referred to as a virtualstimulation site. Advantageously, this possibility of using differentmapping schemes between n SP analysis channels and m ICS stimulationchannels to thereby produce a large number of virtual and otherstimulation sites provides a great deal of flexibility with respect topositioning the neural excitation areas in a location that proves mostbeneficial to the patient.

Still with reference to FIG. 2B, in various embodiments the speechprocessing circuitry 16 includes all of the circuitry from point (C) topoint (A). In prior art cochlear implant systems, the entire SPcircuitry was housed in a speech processor that was part of the external(or non-implanted) portion of the system. That is, in such prior artsystems, only the ICS 21, and its associated electrode array, wereimplanted, as indicated by the bracket labeled “Imp1” (for “Implant-1”).This means that in such prior art systems, the signal passing throughthe serial data stream at point (A) is also the signal that must passthrough the transcutaneous communication link from the external unit tothe implanted unit. Because such a signal contains all of the definingcontrol data for the selected speech processing strategy, for all mstimulation channels, it therefore has a fairly high data rateassociated therewith. As a result of this high data rate, either thesystem operation must be slowed down, which is generally not desirable,or the bandwidth of the link must be increased, which is also notdesirable because the operating power increases.

In contrast to prior art systems, a modem cochlear implant system, suchas the CII Bionic Ear system, or the HiRes90K system, manufactured byAdvanced Bionics Corporation of Sylmar, Calif., advantageously includesat least a portion of the speech processor 16 within the implantedportion of the system. For example, a cochlear implant system may placethe Pulse Table 42 and arithmetic logic unit (ALU) 43 inside of theimplanted portion, as indicated by the bracket labeled “Imp2” in FIG.2B. Such partitioning of the speech processor 16 offers the advantage ofreducing the rate of the data that must be passed from the externalportion of the system to the implanted portion. That is, the data streamthat must be passed to the implanted portion Imp2 comprises the signalstream at point (B). This signal is essentially the digitized equivalentof the modulation data associated with each of the n analysis channels,and (depending upon the number of analysis channels and the samplingrate associated with each) may be significantly lower than the data rateassociated with the signal that passes through point (A). Hence,improved performance without sacrificing power consumption may beobtained with a bionic ear implant.

In other embodiments, cochlear implant systems may incorporate more andmore of the speech processor 16 within the implanted portion of thesystem. For example, a fully implanted speech processor 16 wouldincorporate all of the SP in the implanted portion, as indicated by thebracket labeled Imp3 in FIG. 2B. Such a fully implanted speech processoroffers the advantage that the data input into the system, i.e., the datastream that passes through point (C), need only have a data ratecommensurate with the input signal received through the microphone 18 orthe auxiliary input port 17.

FIGS. 3A and 3B respectively show a conventional in-the-ear hearing aid50 and a behind-the-ear hearing aid 52, such as those illustrated inU.S. Pat. Nos. 6,700,983; 6,658,125; 6,522,764; 5,201,006; 5,033,090;5,357,576; 5,204,917; and 4,051,330; incorporated herein by reference.Both hearing aids 50 and 52 may include electronics 51 and 53 (e.g.,such as those disclosed in the prior art) capable of controlling certainauditory stimulation parameters for a patient with residual hearing.Microphones 54 and 55 sense acoustic signals and convert the sensedsignals to corresponding electrical signals, and thus may be consideredacoustic transducers. The electrical signals are then output asamplified sound by the internal electronics 51 and 53 to the ear of apatient with residual hearing. Either hearing aid 50 or 52, or similarhearing aids, include optional input ports through which either auditoryor electrical signals can be input to the hearing aids 50 or 52. Invarious embodiments, such input ports include a port 56 for a directwire connection, a port for a wireless connection, a port in the form ofan audio shoe 57 which attaches to either hearing aid 50 or 52 andincludes a wire connection 58 or wireless connection to an auxiliarydevice. Auxiliary devices, such as the computer, palm pilot, and otherinterface units shown in FIGS. 4A-4C can thus communicate with thehearing aids 50 and 52 in order to read, map, evaluate, assess, and/ormodify the operating acoustic stimulation parameters of the hearing aids50 and 52. Thus, similar to the cochlear implant system described above,the parameters of a hearing aid system in various example embodimentsare also programmed, or fit, to maximize the hearing experience of apatient.

Embodiments of the present invention can include an electric-acousticprocessor in addition to, or as an alternative to, the cochlear implantsystems and hearing aids described above. An electric-acoustic processorsystem, as with the example embodiment shown in FIG. 4C, can include anycombination of the elements of cochlear implant systems and hearing aidsystems, as needed, to facilitate a device capable of providing bothacoustic stimulation signals to the acoustic sensing organs of the earand electric stimulation signals to the auditory nerve of the same ear.Thus, in various embodiments, an electric-acoustic processor providesboth acoustic and electric stimulation to the same ear of a patient withresidual hearing. As with both the hearing aid system and the cochlearimplant system described above, the electric-acoustic system can beprogrammed, or fit, to a particular patient so as to maximize or atleast improve the hearing of that patient.

Embodiments of the present invention include systems and methods ofreading, mapping, evaluating, assessing, and/or modifying, or fitting,the various electric and acoustic stimulation parameters of at least onehearing device (e.g., a hearing device similar to those describedabove). Many patients with residual, yet limited, hearing can employ acombination of devices that provide acoustic and electric stimulation.For example, a particular patient with residual hearing in one ear andprofound deafness in another ear can use a hearing aid to amplify thesound in the ear with residual hearing and a cochlear implant system toprovide electrical stimulation to the auditory nerve of the patient'sprofoundly deaf ear. Similarly, a patient can employ anelectric-acoustic processor to provide both acoustic and electricstimulation to the auditory organs and auditory nerve of the same ear.These patients often suffer from a lack of coordination or orchestrationof the various parameters of their various hearing devices.

For individuals with hearing sensitivity measure within normal limits,e.g., at frequencies of about <1 kHz, sub-optimal hearing results may beproduced by perceptual channel interaction between the various devicesor by redundant acoustic information. Redundant acoustic informationprovided to the patient by the various devices may give rise toperceptual interference. Such interference makes it difficult for apatient to make sense of certain sounds and noises, thus decreasing thehearing comprehension of the patient. Thus, it is helpful to havetechniques and systems that permit a clinician to orchestrate theacoustic and electric stimulation operations of a patient with residualhearing employing such devices so as to enhance the collectiveperformance of these devices and maximize the hearing comprehension ofthe patient.

Example fitting system configurations are illustrated in FIGS. 4A-4C.These fitting configurations, or other configurations, can be used toprovide orchestrated fitting or modification of acoustic and electricstimulation parameters of at least one hearing device, such as acochlear implant, a hearing aid, or an electric-acoustic processor in apatient (e.g., with residual hearing).

FIG. 4A shows a diagram of basic components used to fit a patient with acochlear implant system and a hearing aid. The cochlear implant systemis as shown in FIG. 2A; and a SP 16 is linked to an ICS 21 which isconnected to an electrode array 48. A microphone 18 is also linked tothe SP 16 through a suitable communication link 24. A laptop computer170, or other type of computer, or equivalent device, is coupled to theSP 16 through an interface unit (IU) 20, or equivalent device. The typeof linkage 23 established between the IU 20 and the SP 16 can varydepending upon whether the SP 16 is implanted or not. Any suitablecommunications link 23 may be used, as is known in the art, and thus thedetails of the link 23 are not important for purposes of the presentinvention. It should be noted that in some embodiments, the IU 20 isincluded within the computer 170 (for example, as a communicationsinterface already present within the computer, e.g., a serial port orother built-in port, or an IR port).

The computer 170, with or without the IU 20, provides input signals tothe SP 16 that simulate acoustical signals sensed by the microphone 18(or received through the auxiliary input port 17 (FIG. 2A) and/orprovides command signals to the SP 16. In some instances, e.g., whentesting the patient's threshold levels, the signals generated by thecomputer 170 replace the signals normally sensed through the microphone18. In other instances, e.g., when testing the patient's ability tocomprehend speech, the signals generated by the computer 170 providecommand signals that supplement the signals sensed through themicrophone 18.

Also as seen in FIG. 4A, the hearing aid system 52 is as shown in FIG. 3and includes the internal electronics 53, the microphone 54, and theaudio shoe, or boot, 57 with accompanying communications wire 58. Thelaptop computer 170, or other type of computer, or equivalent device, iscoupled to the audio boot 57 through an audio interface unit (AIU) 60,or equivalent device. Any suitable communications link between thecomputer 170 and the AIU 60, and between the AIU 60 and the audio boot57, can be used, as is known in the art, and thus the details of suchinterfaces are not important for purposes of the present invention. Itshould be noted that for some applications, the AIU 60 is includedwithin the computer 170 (for example, as a communications interfacealready present within the computer, e.g., a serial port or otherbuilt-in port, or an IR port).

The computer 170, with or without the AIU 60 and/or audio boot 57,delivers signals to the electronics 53 of the hearing aid 52 thatsimulate acoustical signals sensed by the microphone 54. The computer170 also delivers command signals to the electronics 53. In someinstances, e.g., when testing the patient's threshold levels, thesignals generated by the computer 170 replace the signals normallysensed through the microphone 54. In other instances, e.g., when testingthe patient's ability to comprehend speech, the signals generated by thecomputer 170 provide command signals that supplement the signals sensedthrough the microphone 54.

In an example embodiment, the laptop computer 170 (or equivalent device)provides a display screen 15 on which selection screens, stimulationtemplates and other information may be displayed and defined. In such anembodiment, the computer 170 provides a mechanism for the audiologist orother medical personnel, or even the patient, to easily select and/orspecify a particular pattern of stimulation parameters that can be usedthereafter, even if for just a short testing period, regardless ofwhether the stimulation pattern is simple or complex. The variousscreens, templates, and other information can be separated for eachrespective hearing device being fitted for a patient. Alternatively, thescreens, templates, and other information can be combined in a way thatpermits the individual controlling the fitting process to easilysimultaneously or sequentially view and modify the parameters of thedevice(s) being fitted.

Also shown in FIG. 4A is a printer 19, or other auxiliary device, whichmay be connected to the computer 170, if desired, in order to allowneeded support functions such as providing a record of the selectioncriteria, stimulation templates and pattern(s) that have been selectedand/or specified to be printed.

FIG. 4B illustrates an alternative fitting system, in which the ICS 21and the hearing aid 52 are linked to a speech processor configured oremulated within a palm personal computer (PPC) 11, such as a Palm Pilot,or equivalent processor, commercially available, e.g., from HewlettPackard. In the illustrated example embodiment, the PPC 11 includes itsown display screen 15′ on which graphical and textual information can bedisplayed. In use, the PPC 11 is linked, e.g., through an infrared link23′, to another computer, 170, as necessary. By way of example, thefunctions of the SP and related devices (i.e., the functions thatsupport fitting of the hearing aid 52) are stored in a flashcard (aremovable memory card that can be loaded into the PPC 11), therebyenabling the PPC 11 to perform the same functions of those elementsencircled by the dashed lines 13 and/or 62 in FIG. 4A. The PPC 11 iscoupled to the ICS 21 through a suitable data/power communications link14′ and is coupled to the hearing aid 52 through a suitable data/powercommunications link 58′.

The ICS 21 and the hearing aid 52 of FIGS. 4A and 4B are suitable forbeing situated in the same ear (ipsilateral) or contralateral ears of apatient (e.g., with residual hearing).

FIG. 4C illustrates an alternative fitting system that can also be usedwith an electric-acoustic processor system 70 situated in one ear(ipsilateral) of a patient (e.g., with both residual hearing and theneed for electrical stimulation for the same ear). In FIG. 4C, theelectric-acoustic processor system 70 includes a speech processor 72 andinternal acoustic electronics 74 which are linked with the computer 170directly through wired or wireless data/power communications link 76.Alternatively, an auxiliary support unit (not shown) such as the IU 20or AIU 60 of FIG. 4A can be used to supplement the communication link 76between the system 70 and the computer 170. In this example embodiment,the system 70 also includes a microphone 78 capable of performing one ormore of the microphone functions described in reference to the variousembodiments of the present invention.

The computer 170 is configured with software to control reading,displaying, delivering, receiving, assessing, evaluating, and/ormodifying both acoustic and electric stimulation data sent to the system70. In an example embodiment, the electric-acoustic processor system 70is configured to deliver both acoustic stimulation to the auditorysensory organs of the ear and electric stimulation to the auditory nerveof the same ear. Thus, the acoustic stimulation elements and theelectrical stimulation elements interact with the computer 170 and otherelements of systems of the present invention in a similar manner as theelectric stimulation elements of a cochlear implant system and acousticstimulation elements of a hearing aid as discussed through thisdescription of the invention. In various embodiments, the acoustic andelectric stimulation elements of the system 70 can alternatively act ina coordinated effort, e.g., under the direction of a program providedwithin the speech processor 72 or a similar memory element.

FIG. 4C further illustrates alternative embodiments wherein the speechprocessor 16 and the ICS 21 of a cochlear implant system and/or ahearing aid 52 can be simultaneously situated in a patient's earcontralateral to the electric-acoustic system 70. Other embodimentsinclude a second electric-acoustic processor system situated in apatient's ear contralateral to the ear of the electric-acoustic system70.

As illustrated generally in FIG. 5, advantageously, all of the stimuliused during the sound processor setting procedure (or fitting process)can be generated through a software module 110 that is incorporated intothe computer 170, or equivalent processor.

In another variation of the present invention, the software module, orequivalent processor, used to generate the stimuli used is acousticallylinked with the microphones 18, 54, 55, and 78 used by the varioushearing devices of the present invention (see FIGS. 4A-4C). That is, themodulated stimuli are, in some embodiments, inputted into the hearingdevices via the microphone link rather than through an interface unit,an auxiliary port, or another direct connection between the computer 170and the hearing devices.

In operation, the level of the stimuli provided during the fittingprocess can be adjusted according to known perceptual loudness contoursderived from normal hearing individuals (minimal audible field) or fromknown acoustic phenomena, such as the long-term spectrum of speech.Thus, stimuli can be delivered at the electrical equivalent of thelong-term spectrum of speech, at a level representing the detectionabilities of normal hearing individuals, or at any point in between.

Referring to FIG. 6, in an example embodiment, a method 600 formodifying the parameters of multiple hearing devices for a patient withresidual hearing includes the following steps which can be performed inany enabling order. At step 602, a computer is provided that controlsand displays software that is configured to be capable of modifying theparameters of at least one of a hearing aid and the acoustic elements ofan electric-acoustic processor and at least one of a cochlear implantspeech processor and the electric elements of an electric-acousticprocessor when the computer is in communication with any of the hearingaid, the cochlear implant speech processor, the electric elements of theelectric-acoustic processor, and the acoustic elements of theelectric-acoustic processor. At step 604, communication is establishedbetween the computer and at least one of the hearing aid and theacoustic elements of the electric-acoustic processor and at least one ofthe cochlear implant speech processor and the electric elements of theelectric-acoustic processor. The software is used to provideinstructions for at least one of acoustic stimulation to the hearingaid, electric stimulation to the cochlear implant speech processor,electric stimulation to the electric-acoustic processor, and acousticstimulation to the electric-acoustic processor. At step 606, a baselinequestionnaire is administered to a patient in an isolated sound boothwearing at least one of the hearing aid and the acoustic elements of theelectric-acoustic processor and at least one of the cochlear implantspeech processor and the electric elements of the electric-acousticprocessor in which the patient is asked to rate the sound quality of thequestions or stimuli, e.g., presented on a 5-point scale for each of thehearing devices respectively (the other hearing devices being turned offduring the testing of a particular device) and then in combination inorder to verify and set appropriate baseline settings. At step 608, atleast one of the paradigms described in reference to FIGS. 7 and 8, orsimilar paradigms, are employed.

Referring to FIG. 7, in an example embodiment, a paradigm 700 includesthe following steps which can be performed in any enabling order. Atstep 702, the external microphones of each respective hearing device areturned off so as to avoid unwanted environmental noise and sounds. Atstep 704, speech stimuli (such as the sounds of the Ling 5 sound test:/a/, /u/, /i/, /sh/, and /s/) from audio files on a computer arepresented to the patient via direct connection from the computer to eachof the hearing devices respectively and in combination. At step 706, anRMS (or constant) energy is set for each speech stimulus, for example,by routing the output of the computer through a manual attenuator (e.g.,Pasternak 50B). At step 708, the trimmer of any audio shoes employed isset to minimal attenuation. At step 710, the loudness of each speechstimulus at various levels of loudness based on patient feedback isplotted. At step 712, the loudness level of each speech stimulus isadjusted at the most comfortable level for the patient. At step 714, theparameters of the processors of the respective hearing devices aremanipulated through a live speech screen, e.g., shown in the outputadjustment window of a software program presented on the computer. Atstep 716, the modified parameters are outputted to the various hearingdevices to change the acoustic and/or electric stimulation parameters ofthe various hearing devices.

Referring to FIG. 8, in another example embodiment, a paradigm 800includes the following steps which can be performed in any enablingorder. At step 802, if desired, the external microphones of eachrespective hearing device are turned off so as to avoid unwantedenvironmental noise and sounds. At step 804, narrowband noise (NBN)stimuli are presented (e.g., at octave and inter-octave intervals fromaudio files on a computer, or a loudspeaker) to the patient via directconnection from the computer to each of the hearing devices respectivelyand in combination. At step 806, NBN stimuli are calibrated in decibelsound pressure level (dBSPL) for the patient. At step 808, the loudnessof each speech stimulus at various levels of loudness based on patientfeedback is plotted. At step 810, the loudness level of each speechstimulus is adjusted at the most comfortable level for the patient. Atstep 812, the parameters of the processors of the respective hearingdevices are manipulated through a live speech screen, e.g., shown in theoutput adjustment window of a software program presented on thecomputer. At step 814, the modified parameters are outputted to thevarious hearing devices to change the acoustic and/or electricstimulation parameters of the various hearing devices.

While the invention herein disclosed has been described by means ofspecific embodiments and applications thereof, numerous modificationsand variations could be made thereto by those skilled in the art withoutdeparting from the scope of the invention set forth in the claims.

What is claimed is:
 1. A method for modifying the parameters of multiplehearing devices, comprising: providing a user interface that allows auser to modify parameters of at least one of (a) a hearing aid and acochlear implant speech processor and (b) the acoustic and electricelements of an electric-acoustic processor using software configured toprovide instructions to the hearing aid and the cochlear implant speechprocessor, or to the acoustic and electric elements of theelectric-acoustic processor, situated in the same ear for generating orapplying both acoustic stimulation signals to the acoustic sensingorgans of the ear and electric stimulation signals to the auditory nerveof the same ear; wherein the hearing aid and the acoustic elements ofthe electric-acoustic processor are devices that provide acousticstimulation signals to the acoustic sensing organs of the ear, theacoustic stimulation signals being sound waves directed into the earcanal; wherein the cochlear implant speech processor and the electricelements of the electric-acoustic processor are devices that provideelectric stimulation signals to the auditory nerve of the ear, theelectric stimulation signals being stimulation current applied toelectrodes implanted within the cochlea of the ear.
 2. The method ofclaim 1, wherein: the user interface is configured to allow the user tomodify, with the software, the parameters of the electric-acousticprocessor when the electric elements of the electric-acoustic processorare situated ipsilateral to the acoustic elements of theelectric-acoustic processor.
 3. The method of claim 1, wherein: thesoftware is configured to provide instructions when at least one of thehearing aid and the acoustic elements of the electric-acoustic processorare situated contralateral to at least one of the cochlear implantspeech processor and the electric elements of the electric-acousticprocessor.
 4. The method of claim 1, further comprising: mapping audioinformation to electrode contact position with the software in a patientwith a cochlear implant.
 5. The method of claim 1, further comprising:at least one of simultaneously and sequentially outputting instructionscapable of modifying acoustic and electric parameters to determineinteraction between multiple channels in the at least one of the hearingaid, the acoustic elements of the electric-acoustic processor, thecochlear implant speech processor, and the electric elements of theelectric-acoustic processor.
 6. The method of claim 1, furthercomprising: assessing, with the software, the proper sequencing ofacoustic and electric events for at least one of the hearing aid and theacoustic elements of the electric-acoustic processor and at least one ofthe cochlear implant speech processor and the electric elements of theelectric-acoustic processor.